Optical detector

ABSTRACT

Disclosed herein is an optical detector at least including: a first substrate in which a plurality of wells are formed; a second substrate in which a heating section is provided to heat the wells; a third substrate in which a plurality of photoirradiation sections are provided in alignment with the wells; and a fourth substrate in which a plurality of photodetection sections are provided in alignment with the wells.

CROSS REFERENCES TO RELATED APPLICATIONS

The present application is a continuation of U.S. patent applicationSer. No. 14/581,161, filed Dec. 23, 2014, which application is acontinuation of U.S. patent application Ser. No. 12/775,044, filed May6, 2010, issued as U.S. Pat. No. 8,945,911 on Feb. 3, 2015, whichapplication claims priority to Japanese Priority Patent Application JP2009-187342 filed in the Japan Patent Office on Aug. 12, 2009, and inJapanese Priority Patent Application JP 2009-117731 filed in the JapanPatent Office on May 14, 2009 the entire contents of which is herebyincorporated by reference.

BACKGROUND

The present application relates to an optical detector and, moreparticularly, to an optical detector for use in gene expressionanalysis, infectious disease testing, gene analysis such as SNP (SingleNucleotide Polymorphism) analysis, protein analysis, cell analysis andother analyses.

Recent years have seen an increasing commercialization of hybridizationdetection techniques including DNA (deoxyribonucleic acid) chip or DNAmicroarray. DNA chip is a large number of varied DNA probes packed andimmobilized on a substrate surface. Detection of hybridization on thesubstrate surface of this DNA chip allows for all-inclusive analysis ofgene expression and other processes in cells and tissues.

The data obtained from this micro array is verified by means of therealtime PCR (Polymerase Chain Reaction) method. This is a standardapproach for quantitative analysis of nucleic acid in trace amounts. Therealtime PCR method permits amplification of DNA and other targetseveral-hundreds-of-thousand-fold by repeating the amplification cycleincluding “thermal denaturation, annealing with a primer and polymeraseelongation reaction.” The realtime PCR method is used to monitor inrealtime the PCR amplification product obtained as described above forquantitative analysis of nucleic acid in trace amounts. In this method,a dedicated device incorporating a thermal cycler and fluorescencespectrophotometer in a single unit is used to monitor in realtime thePCR amplification product.

In addition to the PCR method, there are other nucleic acidamplification techniques such as the SMAP (SMart Amplification Process),LAMP (Loop-Mediated Isothermal Amplification), NASBA (Nucleic AcidSequence Based Amplification) and ICAN (Isothermal and Chimericprimer-initiated Amplification of Nucleic acid) methods designed toisothermally amplify DNA. Here, however, a description will be givenbelow of the realtime PCR detection method, a typical amplificationmethod.

First, if only the gene target of interest can be amplified using ahighly specific primer, the intercalator method using SYBR (registeredtrademark) GreenI is employed.

In the intercalator method, an intercalator is used which emitsfluorescence when bonded to a double-chain DNA. Fluorescence is emittedby bonding this intercalator to a double-chain DNA produced in thecourse of PCR reaction and irradiating excitation light onto theintercalator. The amount of PCR amplification product generated ismonitored by detecting the intensity of this fluorescence. Thisintercalator method requires no designing or synthesis of a fluorescentlabeling probe specific to the target, making it readily applicable formeasurement of a wide variety of targets.

On the other hand, if it is necessary to distinguish between sequenceshaving similar structures or if multiplex detection is required as fortyping of SNPs, a probe method is used. The TaqMan (registeredtrademark) probe method is an example of such a probe method and uses,as a probe, an oligonucleotide having its 5′ end modified with aquencher substance and its 3′ end modified with a fluorescent substance.

The TaqMan probe specifically hybridizes to a template DNA in theannealing step. The same probe does not emit fluorescence whenirradiated with excitation light due to the presence of a quenchersubstance on the probe. In the elongation reaction step, however, theTaqMan probe hybridized to the template DNA is decomposed by a 5′ to 3′exonuclease activity of the TaqDNA polymerase. As a result, thefluorescent substance is liberated from the probe, eliminating theinhibition by the quencher and causing fluorescence to be emitted. Theamount of PCR amplification product generated can be monitored bydetecting the intensity of this fluorescence.

A detailed description will be given below of the steps for quantifyinggene expression level by the above methods using realtime PCR. First,PCR is performed on a serially diluted standard sample of knownconcentration as a template to find the threshold cycle (Ct value)required to reach a given amount of amplification product. A standardcurve is prepared by plotting this Ct value along the horizontal axisand the initial DNA amount along the vertical axis. Based on this, PCRreaction is performed on a sample of unknown concentration under thesame conditions to find the Ct value. Finally, the DNA amount ofinterest in the sample is measured from this Ct value and standardcurve.

As for the techniques related thereto, JP-T-2003-525617 and JapanesePatent Laid-Open No. 2001-136954 (hereinafter referred to as PatentDocuments 1 and 2, respectively) disclose, for example, temperaturecontrol and other techniques during amplification reaction.

SUMMARY

An optical detector must measure the reactions taking place in the wellsin realtime. For example, an optical detector for use in nucleic acidamplification detection must measure the nucleic acid amplificationprocess in realtime. As a result, such a detector must include not onlywells in which reactions are conducted but also a variety of means. Suchmeans include heating means adapted to accelerate the respectivereactions, photoirradiation means adapted to irradiate excitation lightand photodetection means adapted to detect fluorescence and other lightfrom the wells.

A recent significant advance in biotechnology holds promise fordevelopment of more compact optical detectors with higher accuracy.

In light of the foregoing, according to the present invention, a highperformance and compact optical detector that can be readilymanufactured is provided.

First, an embodiment of the present application provides an opticaldetector. The optical detector includes at least first, second, thirdand fourth substrates. A plurality of wells are formed in the firstsubstrate. Heating means is provided in the second substrate to heat thewells. A plurality of photoirradiation means are provided in the thirdsubstrate. The plurality of photoirradiation means are aligned with thewells. A plurality of photodetection means are provided in the fourthsubstrate. The plurality of photodetection means are aligned with thewells.

In the optical detector according to an embodiment, the necessary meansare provided one in each substrate. This makes it possible tomanufacture the optical detector simply by stacking the substrates oneon the other.

The heating means may be provided across the second substrate.Alternatively, the plurality of heating means may be aligned with thewells on the second substrate.

The heating means that can be used for the optical detector according toan embodiment is not specifically limited in structure so long as thewells can be heated. As an example, the heating means can be configuredby patterning transparent electrodes in the second substrate.

In this case, ITO and ZnO electrodes are among transparent electrodesthat can be used.

On the other hand, the wells can be heated from either side of the wellsby the heating means. For example, the second substrate may be stackedon the side of the first substrate facing the third or fourth substrate.Alternatively, the second substrates may be stacked one on each side ofthe first substrate in such a manner as to sandwich the first substrateso as to heat the wells from both sides.

The optical detector according to an embodiment need only include atleast the first to fourth substrates. However, a plurality of condenserlenses may be arranged between the photoirradiation means and wells orbetween the wells and photodetection means.

The optical detector according to an embodiment can serve as a nucleicacid amplification detector capable of detecting nucleic acidamplification in the wells.

In this case, the optical detector according to an embodiment permitsnucleic acid amplification not only by means of the PCR (PolymeraseChain Reaction) method, a widely used technique for gene amplification,but also by means of isothermal amplification methods such as the SMAP(SMart Amplification Process) method, LAMP (Loop-Mediated IsothermalAmplification) method, ICAN (Isothermal and Chimeric primer-initiatedAmplification of Nucleic acids) method and NASBA (Nucleic AcidSequence-Based Amplification) method.

In the optical detector according to an embodiment, the necessary meansare provided one in each substrate and aligned with each other. Thismakes it possible to readily manufacture a high performance and compactoptical detector simply by stacking the substrates one on the other.

Additional features and advantages are described herein, and will beapparent from the following Detailed Description and the figures.

BRIEF DESCRIPTION OF THE FIGURES

FIG. 1 is a sectional schematic view schematically illustrating a firstembodiment of an optical detector;

FIG. 2 is a plan schematic view schematically illustrating an example ofa first substrate of the optical detector according to an embodiment;

FIG. 3 is an A-A fragmentary sectional view as seen from an arrow A-A ofthe example of the first substrate shown in FIG. 2;

FIG. 4 is a sectional schematic view schematically illustrating a secondembodiment of the optical detector;

FIG. 5 is a sectional schematic view schematically illustrating a thirdembodiment of the optical detector;

FIG. 6 is a sectional schematic view schematically illustrating a fourthembodiment of the optical detector;

FIG. 7 is a sectional schematic view schematically illustrating a fifthembodiment of the optical detector;

FIG. 8 is a sectional schematic view schematically illustrating a sixthembodiment of the optical detector;

FIG. 9 is a sectional schematic view schematically illustrating aseventh embodiment of the optical detector; and

FIG. 10 is a sectional schematic view schematically illustrating aneighth embodiment of the optical detector.

DETAILED DESCRIPTION

The present application will be described in detail below with referenceto the figures according to an embodiment. It should be noted that thedescription will be given in the following order:

-   -   (1) Wells 111 (first substrate 11)    -   (2) Heating portion 121 (second substrate 12)    -   (3) Photoirradiation portion 131 (third substrate 13)    -   (4) Photodetection portion 141 (fourth substrate 14)    -   (5) Condenser lenses 151 a, 151 b and 151 c    -   (6) Optical filters 161 a, 161 b and 161 c    -   (7) Apertures 181 a, 181 b, 181 c, 181 d and 181 e and partition        walls    -   (8) Specific example of the optical detector

FIG. 1 is a sectional schematic view schematically illustrating a firstembodiment of an optical detector 1 according to the present invention.The optical detector 1 includes at least a (1) first substrate 11, (2)second substrate 12, (3) third substrate 13 and (4) fourth substrate 14.The optical detector 1 may further include (5) condenser lenses 151 aand 151 b and (6) optical filters 161 a and 161 b as necessary.

The materials used to form the respective substrates are notspecifically limited, and any of those materials that can be commonlyused for optical detectors such as nucleic acid amplification detectorscan be selected as desired. In the present invention, it is particularlypreferred that the substrates be made of a light-transmitting materialsuch as polycarbonate, polyolefin-based resin, acryl-based resin orother plastic resin, PDMS (polydimethylsiloxane) or other silicon-basedresin or glass so as to allow light to transmit through the substrates.

A detailed description will be given below of the substrates of theoptical detector 1 according to an embodiment and the means provided inthe substrates.

(1) Wells 111 (First Substrate 11)

A plurality of wells 111 are formed in the first substrate 11. The wells111 are reaction fields where interactions proceed between thesubstances such as nucleic acid amplification, hybridization, nucleicacids, proteins and cells.

If the optical detector 1 according to an embodiment is used as anucleic acid amplification detector, any of the methods used as the geneamplification methods can be selected as desired for nucleic acidamplification. For example, among the methods that can be used are thePCR method, SMAP method, LAMP method, ICAN method, NASBA method, SDA(Strand Displacement Amplification) method, TMA (Transcription-MediatedAmplification) and TRC (Transcription-Reverse transcription Concerted)method. Of these methods, an isothermal amplification method such as theSMAP, LAMP, ICAN or NASBA method should preferably be used. Theisothermal amplification methods do not require any temperaturevariation as does the PCR method, thus eliminating the need for a heatradiation mechanism and making the device as a whole compact.

In the optical detector 1 according to an embodiment, excitation lightis irradiated from one side of the first substrate 11 in which the wells111 are formed so as to detect light such as fluorescence emitted fromthe substances in the wells 111 from the other side of the firstsubstrate 11. Therefore, it is preferred that the wells 111 be made of alight-transmitting material such as polycarbonate, polyolefin-basedresin, acryl-based resin or other plastic resin, PDMS(polydimethylsiloxane) or other silicon-based resin or glass.

It should be noted that the method used to introduce the substances intothe wells 111 is not specifically limited, and any of the publicly knownmethods can be used as desired. As illustrated in FIGS. 2 and 3, forexample, a flow path F leading to the wells 111 can be formed in thesubstrate to introduce the substances into the wells 111 via the flowpath F.

(2) Heating Portion 121 (Second Substrate 12)

A heating portion 121 is provided in the second substrate 12 to heat thewells 111. The heating method used for the heating portion 121 is notspecifically limited, and any of the publicly known methods can be usedas desired. For example, electrodes may be patterned in the substrate.

The heating portion 121 is not specifically limited in form so long asit can heat the wells 111. As illustrated in FIG. 1, the heatingportions 121 may be provided across the second substrate 12 to heat thewells 111 as a whole. Alternatively, the heating portions 121 may bealigned, one with each of the wells 111, as illustrated in a secondembodiment of FIG. 4. If the heating portions 121 are provided, one foreach of the wells 111, it is possible to control the heating temperatureand time for each of the wells with precision.

If the heating portions 121 are provided, one for each of the wells 111,it is preferred that the heating portion 121 be designed to be largerthan the wells 111. Although the heating efficiency of the heatingportion 121 may be lowered at the edges, the heating portion 121 largerthan the wells 111 can suppress the reduction in heating efficiency atthe edges.

As for the control method, temperature sensors may be provided in theheating portion 121, although not shown, so as to feed back the measuredtemperatures, thus permitting accurate control of the temperatures.

Further, if the heating portions 121 are provided, one for each of thewells 111, it is possible to locally heat the wells 111, thuscontributing to reduced power consumption. Assuming, for example, thatthe nine wells of about 100 nL each are heated at 60° C. for 30 minutesby means of the SMAP method, if nine ITO electrodes are used, the powerconsumption is on average about 0.6 W. On the other hand, if Peltierdevices are used, the power consumption is on average about 10 W, whichis an order of a magnitude greater than if ITO electrodes are used.

Further, if the heating portions 121 are provided, one for each of thewells 111, it is possible to control the temperatures of the individualwells 111, thus preventing variations in temperature from one well toanother.

Still further, using electrodes as the heating portion 121 allows forreduction in size of the detector. For example, if Peltier devices areused, ceramic plates for thermal diffusion must be provided on top ofthe Peltier devices to provide uniform temperature distribution.Further, Peltier devices require heatsinks and fans for heat radiationand absorption, thus requiring a thickness of about 30 mm. On the otherhand, transparent electrodes such as ITO or ZnO electrodes require onlythe thickness of the second substrate (e.g., 0.7 mm) for patterning thesame electrodes, thus contributing to reduced size of the detector as awhole.

It should be noted that the heating portion 121 using electrodes may becombined with a Peltier device as illustrated in a third embodiment ofFIG. 5. If, for example, a constant-temperature Peltier device 171 of 20to 40° C. is used in combination, hunting of the heating portion 121using electrodes during temperature control will be suppressed, thusproviding stable temperature regulation.

The second substrate 12 having the heating portion 121 is stacked on thefirst substrate 11 having the wells 111 formed therein. As a result, theheating portion 121 must also transmit excitation light fromphotoirradiation portion 131 or fluorescence or other light from thesubstances. Therefore, if electrodes are used as the heating portion121, transparent electrodes must be used. In this case, ITO and ZnOelectrodes are among transparent electrodes.

The wells 111 can be heated by the heating portion 121 from either sideof the wells 111. The direction of heating is not limited to an upwarddirection from bottom in the figure as in the first embodiment of FIG.1, second embodiment of FIG. 4 and third embodiment of FIG. 5. Instead,the wells 111 may be heated from top in the figure as in a fourthembodiment of FIG. 6.

If, for example, transparent electrodes such as ITO or ZnO electrodesare used as the heating portion 121, the transmittance thereof maydecline as a result of heating. However, if the heating portions 121 areprovided above the wells 111 in the figure (on the side facing the thirdsubstrate 13 which will be described later), light emitted from thewells 111 can be detected properly by photodetection portions 141 whichwill be described later, thus providing improved S/N ratio.

Further, the wells 111 may be, for example, heated from both sides as ina fifth embodiment of FIG. 7. Heating the wells 111 from both sidesprovides an advantageous effect in that the well temperatures can bereadily maintained uniform.

The heating portions 121 of the optical detector 1 according to theembodiment of the present invention are provided in the second substrate12. This makes it possible to readily change the heating directionsimply by changing the position where the second substrate 12 is stackedon the first substrate 11 having the wells 111 formed therein. Forexample, if the second substrate 12 is stacked on top of the firstsubstrate 11 in the figure (on the side facing the third substrate 13which will be described later), the wells 111 can be heated from top. Onthe other hand, if the two second substrates 12 are made available andstacked one on either side of the first substrate 11 in such a manner asto sandwich the first substrate 11, the wells 111 can be heated fromboth sides.

Still further, if the second substrate 12 is stacked under the firstsubstrate 11 in the figure (on the side facing the fourth substrate 14which will be described later), it is preferred that the lower side ofthe second substrate 12 be anti-reflection coated, although not shown.Anti-reflection coating is expected to provide 3 to 5% improvement intransmittance in the visible range.

(3) Photoirradiation Portion 131 (Third Substrate 13)

The plurality of photoirradiation portions 131 are provided in the thirdsubstrate 13 in such a manner as to be aligned with the wells 111. Thephotoirradiation portions 131 are designed to irradiate excitationlight, for example, onto the fluorescent substances in the wells 111 andonto the intercalator.

Thanks to the plurality of photoirradiation portions 131 of the opticaldetector 1 according to an embodiment provided in the third substrate 13in alignment with the wells 111, it is possible to irradiate light ontothe wells 111 with accuracy simply by stacking the third substrate andfirst substrate 11 one on the other. This eliminates the need to alignthe photoirradiation portion with the wells 111 for scanning, thusrequiring no drive mechanism adapted to move the photoirradiationportion and contributing to reduced size of the detector.

On the other hand, if excitation light is irradiated from a singlephotoirradiation portion onto the plurality of wells in a singleoperation, a long optical path is required to eliminate chromaticity,making the increase in size inevitable for detectors in related art. Inthe optical detector 1 according to the embodiment of the presentinvention, however, light can be irradiated onto the wells 111 in asingle operation simply by stacking the third substrate 13 having thephotoirradiation portion 131 and the first substrate 11 having the wells111 formed therein one on the other. This also contributes to reducedsize of the detector.

The photoirradiation method that can be used for the photoirradiationportion 131 of the optical detector 1 according to the embodiment of thepresent invention is not specifically limited, and any of the publiclyknown methods can be used as desired. For example, one or two or morephotoirradiation methods can be selected as desired. Among selectableirradiation methods are LED (Light Emitting Diode), semiconductor laserand EL lighting.

The signal acquisition time can be reduced by lighting up thephotoirradiation portions 131 in a single operation and detecting thelight with the photodetection portions 141, which will be describedlater, in a single operation. Alternatively, noise from the adjacentphotoirradiation portions 131 can be reduced by lighting up the sameportion 131 quickly one after the other.

(4) Photodetection Portion 141 (Fourth Substrate 14)

The plurality of photodetection portions 141 are provided in the fourthsubstrate 14 in alignment with the wells 111. The photodetectionportions 141 are designed to detect light from the fluorescentsubstances in the wells 111 and the intercalator so as to monitor theamount of amplification product generated in the wells 111.

Thanks to the plurality of photodetection portions 141 of the opticaldetector 1 according to an embodiment provided in the fourth substrate14 in alignment with the wells 111, it is possible to detect light suchas fluorescence from the wells 111 with accuracy simply by stacking thefourth substrate and first substrate 11 one on the other. Thiseliminates the need to align the photodetection portions with the wells111 for scanning, thus contributing to reduced size of the detector.

The photodetection method that can be used for the photodetectionportion 141 of the optical detector 1 according to the embodiment of thepresent invention is not specifically limited, and any of the publiclyknown methods can be used as desired. Among selectable detection methodsare those using area imaging device such as PD (Photo Diode), chargecoupled device (CCD) and complementary metal oxide semiconductor (CMOS).

(5) Condenser Lenses 151 a, 151 b and 151 c

FIG. 8 is a sectional schematic view schematically illustrating a sixthembodiment of the optical detector 1 according to an embodiment. In thepresent embodiment, a plurality of excitation condenser lenses 151 a areprovided between the photoirradiation portions 131 and wells 111 tocollect light from the photoirradiation portions 131. The opticaldetector 1 according to the embodiment of the present invention permitsaccurate irradiation of light onto the wells 111 simply if the thirdsubstrate and first substrate 11 are stacked one on the other. However,the optical detector 1 permits even more accurate irradiation if theexcitation condenser lenses 151 a are provided as in an embodiment.

Further, in the present embodiment, a plurality of photoreceptioncondenser lenses 151 b are provided between the wells 111 andphotodetection portions 141 to focus light such as fluorescence from thewells 111 onto the photodetection portions 141. The optical detector 1according to an embodiment permits accurate detection of light from thefluorescent substances in the wells and the intercalator simply if thefourth substrate and first substrate 11 are stacked one on the other.However, the levels of fluorescence and other signals can be enhancedfurther if the photoreception condenser lenses 151 b are provided as inthe present embodiment, thus providing improved S/N ratio.

Still further, in the optical detector 1 according to an embodiment, aplurality of second photoreception condenser lenses 151 c may beprovided in addition to the photoreception condenser lenses 151 b as ina seventh embodiment shown in FIG. 9. If the two condenser lenses 151 band 151 c with a short focal distance and high numerical aperture areprovided for each of the wells as the photoreception condenser lenses asdescribed above, it is possible to provide even higher fluorescencecollection efficiency, thus ensuring even higher S/N ratio. Further,close proximity imaging is possible, making it possible to shorten theoptical system and contributing to reduced size of the detector. Stillfurther, distortion of the substrates at the edges can be reducedwithout using a combination of expensive lenses as in a microscope, thusallowing for photodetection at a brightness equivalent to that at thecenter of the substrate. Moreover, crosstalk from the adjacent wells canbe reduced if the focal distance of the second photoreception condenserlenses 151 c is equal to or shorter than that of the firstphotoreception condenser lenses 151 b.

(6) Optical Filters 161 a, 161 b and 161 c

In the optical detector 1 according to an embodiment, the excitationoptical filter 161 a may be provided between the photoirradiationportions 131 and wells 111 (refer to FIGS. 1 and 4 to 10). If theexcitation optical filter 161 a is provided, it is possible toselectively irradiate excitation light of desired wavelength onto thewells 111. The optical detector 1 according to the embodiment of thepresent invention permits accurate photoirradiation onto the wells 111simply if the third substrate and first substrate 11 are stacked one onthe other. However, if the excitation optical filter 161 a is provided,it is possible to selectively irradiate excitation light with moreaccuracy according to the properties of the fluorescent substances inthe wells 111 and the intercalator.

In the optical detector 1 according to an embodiment, the photoreceptionoptical filter 161 b may be provided between the wells 111 andphotodetection portions 141 (refer to FIGS. 1 and 4 to 10). If thephotoreception optical filter 161 b is provided, it is possible toselectively receive light of desired wavelength from among light such asfluorescence from the fluorescent substances in the wells 111 and theintercalator. The optical detector 1 according to the embodiment of thepresent invention permits accurate detection of light from thesubstances in the wells 111 simply if the fourth substrate and firstsubstrate 11 are stacked one on the other. However, if thephotoreception optical filter 161 b is provided, it is possible toselectively obtain light with more accuracy, thus providing improved S/Nratio.

Further, in the optical detector 1 according to an embodiment, a secondphotoreception optical filter 161 c may be provided between the firstsubstrate 11 and first photoreception condenser lenses 151 b in additionto the first photoreception optical filter 161 b as illustrated in aseventh embodiment of FIG. 9. As described above, the insertion of onemore photoreception optical filter enhances removal of excitation lightirradiated from the photoirradiation portion 131, thus providing furtherimproved S/N ratio.

(7) Apertures 181 a, 181 b, 181 c, 181 d and 181 e and partition walls

FIG. 10 is a sectional schematic view schematically illustrating aneighth embodiment of the optical detector 1. In the present embodiment,apertures 181 a, 181 b, 181 c, 181 d and 181 e are provided, one betweenthe excitation optical filter 161 a and second substrate 12, and one oneach side of the photoreception condenser lenses 151 b and 151 c. Itshould be noted that the optical detector 1 according to an embodimentprovides the same advantageous effect if partition walls, although notshown, rather than the apertures 181 a, 181 b, 181 c, 181 d and 181 e,are provided between the lenses.

As described above, the aperture 181 a or partition wall on thephotoirradiation side prevents irradiation of light from thephotoirradiation portion 131 onto the wells 111 other than theassociated one (e.g., adjacent wells), thus providing improved S/Nratio.

On the other hand, the apertures 181 b, 181 c, 181 d and 181 e orpartition walls on the photodetection side provides reduced crosstalkfrom the wells 111 other than the associated one (e.g., adjacent wells),thus providing improved S/N ratio.

The optical detector 1 according to an embodiment described abovepermits a variety of detections and analyses not only on medicalfrontlines but also in other wide ranging fields, including on-sitediagnosis in developing countries and disaster-hit areas, detection ofpathogenic bacteria in food processing plants, food warehouses, grocerystores and restaurants, detection in food-producing areas, environmentaltesting in seas, lakes and rivers and environmental testing fornorovirus in public facilities.

It should be understood that various changes and modifications to thepresently preferred embodiments described herein will be apparent tothose skilled in the art. Such changes and modifications can be madewithout departing from the spirit and scope of the present subjectmatter and without diminishing its intended advantages. It is thereforeintended that such changes and modifications be covered by the appendedclaims.

The invention is claimed as follows:
 1. An optical detecting apparatus configured to detect a signal from a sample in at least one of a plurality of wells, the optical detecting apparatus comprising: heaters configured to control temperatures in the plurality of wells, the heaters including a plurality of pairs of first and second heaters positioned apart to accommodate at least one of the wells in alignment between each respective pair of heaters, the wells being positioned apart from the first and second heaters; light sources configured to illuminate the sample, the light sources being arranged on a first side of the first heaters that is opposed to a well accommodation side of the first heaters; and optical detection elements configured to detect a signal from the sample, the optical detection elements being arranged on a second side of the second heaters that is opposed to a well accommodation side of the second heaters.
 2. The optical detecting apparatus of claim 1, wherein the heaters include patterned transparent electrodes.
 3. The optical detecting apparatus of claim 2, wherein the transparent electrodes are ITO or ZnO electrodes.
 4. The optical detecting apparatus of claim 1, wherein a plurality of condenser lenses are provided, each of the condenser lenses being provided in alignment between respective opposed light sources and first heaters.
 5. The optical detecting apparatus of claim 1, wherein a plurality of condenser lenses are provided, each of the condenser lenses being provided in alignment between respective opposed optical detection elements and second heaters.
 6. The optical detecting apparatus of claim 1, wherein a plurality of condenser lenses are provided, a pair of the condenser lenses being provided in alignment between respective opposed optical detection elements and second heaters.
 7. The optical detecting apparatus of claim 6, wherein an optical filter is provided in alignment between the two condenser lenses for each pair of condenser lenses.
 8. The optical detecting apparatus of claim 1, configured as a nucleic acid amplification detector capable of detecting nucleic acid amplification in the wells.
 9. The optical detecting apparatus of claim 8, wherein an isothermal amplification method is used for the nucleic acid amplification.
 10. The optical detecting apparatus of claim 9, wherein one of the SMAP, that stands for Smart Amplification Process, method, LAMP, that stands for Loop-Mediated Isothermal Amplification, method, ICAN, that stands for Isothermal and Chimeric primer-initiated Amplification of Nucleic acids, method and NASBA, that stands for Nucleic Acid Sequence-Based Amplification, method is selected for the nucleic acid amplification.
 11. The optical detecting apparatus of claim 1, further comprising a constant-temperature Peltier device provided on a side of the optical detection elements such that the optical detection elements are sandwiched between the second heaters and the constant-temperature Peltier device. 